Transseptal closure of a patent foramen ovale and other cardiac defects

ABSTRACT

The present invention provides for therapeutic treatment methods, devices, and systems for the partial or complete closure or occlusion of a patent foramen ovale (“PFO”). In particular, various methods, devices, and systems for joining or welding tissues, in order to therapeutically close a PFO are described. In yet another aspect of the invention, various methods, devices, and systems for the penetration of the interatrial septum enabling left atrial access are also provided.

COPYRIGHT NOTICE

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FIELD OF THE INVENTION

The present invention relates generally to the field of cardiology, and in particular to methods, devices, and systems to close or occlude a patent foramen ovale or “PFO.”

BACKGROUND OF THE INVENTION

A closed foramen ovale is formed after birth when two fetal structures, the septum secundum (“secundum”) and septum primum (“primum”), become fused and fibrose together. Usually, the fusion of these two anatomical structures occurs within the first two years of life ensuring the formation of a normal functioning heart. However, in about 25-27% of the general population, the secundum and the primum either do not fuse or the fusion is incomplete. As a result, a long tunnel-like opening will exist in the interatrial septum (“septum”) which allows communication between the right and left atrial chambers of the heart. This tunnel-like opening is a cardiac defect known as a PFO.

Normally, a PFO will be found near the fossa ovalis, an area of indentation on the right atrial side of the interatrial septum as illustrated in FIGS. 1A and 1B. In most circumstances, a PFO will remain functionally closed or “competent” and blood flow through the PFO will not occur due to the higher atrial pressures in the left atrium that serve to secure the flap-like primum against the secundum and interatrial septum, thereby closing the PFO. See FIGS. 1A and 1B. Nevertheless, in instances of physical exertion or when pressures are greater in the right atrium, inappropriate right-to-left shunting of blood can occur introducing venous blood and elements, such as clots or gas bubbles within the blood, into the left atrium and the systemic atrial system, posing serious health risks including: hemodynamic problems; cryptogenic strokes; venous-to-atrial gas embolism; migraines; and in some cases even death.

Traditionally, open chest surgery was required to suture or ligate closed a PFO. However, these procedures carry high attendant risks such as postoperative infection, long patient recovery, and significant patient discomfort and trauma. Less invasive, or minimally invasive, treatments are preferred and are currently being developed.

To date, most of these non-invasive, or minimally invasive, procedures involve the transcatheter implantation of various mechanical devices to close or occlude a PFO. See FIGS. 2A and 2B. That they are not well suited or designed for the long tunnel-like anatomical shape of a PFO, is a significant drawback of many PFO devices currently on the market including: the Cardia® PFO Closure Device, Amplatzer® PFO Occluder, and CardioSEAL® Septal Occlusion Device, just to name a few. As a result, device deformation and distortion is not uncommon and instances of mechanical failure, migration or even device dislodgement have been reported. Further, these devices can irritate the cardiac tissues at, or near, the implantation site, which in turn can potentially cause thromboembolic events, palpitations, and arrhythmias. Other reported complications include weakening, erosion, and tearing of the cardiac tissues around the implanted devices.

Yet another disadvantage of these mechanical devices is that the occlusion of the PFO is not instantaneous or complete immediately following implantation. Instead, occlusion and complete PFO closure requires subsequent endothelization of these devices. This endothelization process can be very gradual and can take several months or more to occur. Thus, “occlusion” of the PFO is not immediate but can be a rather slow and extended process.

Finally, the procedure to implant these devices can be technically complicated and cumbersome, requiring multiple attempts before the device can be appropriately and sufficiently delivered to the PFO. Accordingly, use of these devices may require long procedure times during which the patient must be kept under conscious sedation posing further risks to patients.

In light of these potentially serious drawbacks, new and improved non-invasive and/or minimally invasive methods, devices, and systems for the treatment of PFO, which either do not require the use of implantable devices or overcome some of the current shortcomings discussed above, are needed. The present invention meets these, as well as other, needs.

SUMMARY OF THE INVENTION

The present invention is directed to methods, devices, and systems for applying energy to join tissues, and in particular for joining the two flap-like tissues, the secundum and primum, that comprise a PFO. Tissues and blood in the human body demonstrate several unique properties when heated; accordingly heat can be used as an effective means for inducing the joining of tissues. Typically, when biological tissues and blood are heated, denaturation, melting, and/or coagulation of tissue and blood proteins, including collagen, takes place, along with the disruption of the cells and cellular walls, allowing intra-and-intercellular fluids and proteins to mix and form a type of “biological glue” which can be used to join tissues together. Yet another response to heat includes the activation of the body's healing mechanisms, which includes the activation of platelets, thrombin, fibrin, etc., and the formation of new scar tissue connections, which serve to join tissues.

A first aspect of the invention provides for methods, devices, and systems for joining tissue structures, and in particular, for joining the secundum and the primum to close or occlude a PFO. In accordance with this aspect of the invention, one method involves coapting the secundum and primum between one or more members and delivering therapeutic amounts of energy in order to join the two tissue structures together. As used herein, “coapt” means the drawing together of separated tissues or other structures. Energy sufficient to raise the native tissue temperatures of the coapted tissues to about 50°-100° C. is applied to the secundum and the primum. In accordance with this first aspect of the invention, various catheters for coapting and joining the primum and secundum are provided and further described herein.

In a second and related aspect of the invention, the primum and secundum are joined at one or more tissue contact sites, or alternatively are joined along a seam. Depending on the technique employed, complete or partial PFO closure can be selectively achieved. Described herein are possible implementations and configurations of heat generating members for creating: (1) a single tissue contact site; (2) a pattern of contact sites forming a seam; or (3) continuous seams having different shapes, for example, circular, curvilinear or straight seams.

A third aspect of the invention provides different methods, devices, and systems for ensuring tight joining of the tissues involving a welding technique. As used herein, “welding” refers to the use of heat in conjunction with pressure (as opposed to heat only) to join tissues together. Energy sufficient to raise the native tissue temperatures to about 50°-100° C. is applied in order to affect tissue welding of the secundum and the primum. Preferably, compressive force is used to not only coapt the primum and the secundum, but also to ensure the efficient and secure tissue welding during heating or energy delivery. To efficiently weld the primum and secundum, the two tissues should be encased between two opposed members that are provided as means to compress the tissues in question. Describe herein are methods and devices including various inflation members and other like devices for encasing, coapting, and compressing the tissue to be welded. As will be better understood in reference to the description provided below, one method for encasing the primum and the secundum between two opposed members is to transseptally deploy and position the two opposed members. As used herein “transseptal” means across or to the other side of the interatrial septum of the heart.

A fourth aspect involves various methods, devices, and systems for transseptally deploying various heating members, compressive members, or other like structures. In accordance with this aspect of the invention, one method involves puncturing the interatrial septum and a creating a passage therethrough so that one or more compressive members, heating members, or any combination thereof, which located at a distal working end of a PFO treatment catheter or catheter assembly, can be passed from one atrium of the heart to the other, preferably from the right to the left atrium.

A fifth aspect of the invention involves various medical kits comprising one or more catheters, puncturing means, guidewires, and/or other related components for therapeutically joining tissues or welding tissues in order to close or occlude a PFO in accordance with the present invention.

A sixth aspect of the invention involves various medical kits comprising one or more catheters, tissue penetrating devices, and other like means for transseptal penetration of the interatrial septum, thus allowing left atrial access. These devices and catheters embody various techniques and other aspects for easily identifying, positioning, and penetrating the septum at a pre-determined location.

A seventh aspect involves methods, devices, and systems for the deployment and implantation of various mechanical devices that represent an improvement over PFO occlusion devices and techniques currently known to those skilled in the art. In a related embodiment, these various devices and implants can be heated fixed or secured inside the patient.

A further aspect of the invention involves the various forms of energy that can be used to affect joining or welding of tissues, including, but not limited to: high intensity focused or unfocused ultrasound; direct heat; radiofrequency (RF); chemically induced heat (as in exothermic reactions), and other types of electromagnetic energy of differing frequencies, such as light (coherent and incoherent), laser, and microwaves can also be used. As described below, tissue heating in accordance with the present invention is char-free and controlled to prevent unintended thermal injury to the surrounding and adjacent cardiac tissues. One or more monitoring methods, devices (such as thermosensors), and systems are provided to ensure controlled and selective tissue heating.

Further understanding of the nature and advantages of the invention may be realized by reference to the remaining portions of the specification and the drawings.

BRIEF DESCRIPTION OF THE DRAWINGS

FIGS. 1A-1D illustrate a heart comprising a PFO, wherein:

FIG. 1A is a cross sectional view of a human heart;

FIG. 1B is a partial, cross-sectional view of an interatrial septum comprising a closed PFO;

FIG. 1C is a partial, cut-away, orthogonal view of the fossa ovalis and the PFO wherein the PFO is shown in phantom; and

FIG. 1D is a partial, cross-sectional view of the interatrial septum comprising an open PFO.

FIG. 2 illustrates the deployment of prior art mechanical occlusive devices inside the tunnel-like opening of a PFO, i.e. “PFO tunnel.”

FIG. 3 is a flow chart illustrating a general treatment method in accordance with the present invention.

FIGS. 4A-4B illustrate a PFO treatment catheter in accordance with the present invention wherein:

FIG. 4A is a perspective view; and

FIG. 4B is a cross-sectional view of one possible implementation of the distal working end of the PFO treatment catheter shown in FIG. 4A

FIG. 5A-5B are cross-sectional view of a interatrial septum comprising a PFO, wherein:

FIG. 5A is a partial, cross-sectional view of the interatrial septum illustrating the preferred region of penetration at a location where the secundum and primum overlap; and

FIG. 5B is a partial, cross-sectional view of the interatrial septum illustrating the transseptal deployment of two opposed members.

FIG. 6A-6B illustrates one embodiment of a PFO treatment catheter in accordance with the present invention wherein:

FIG. 6A illustrates a PFO treatment catheter wherein the two opposed member comprise two inflation members comprising one or more RF electrodes; and

FIG. 6B illustrates yet another embodiment of the PFO treatment catheter shown in FIG. 6A.

FIGS. 7A-7B illustrate yet another embodiment of the present invention wherein PFO treatment catheter comprises a deployable wire assembly.

FIG. 8 illustrates yet another embodiment of a PFO treatment catheter in accordance with the present invention.

FIG. 9 is a perspective view of a PFO treatment catheter assembly comprising a guide catheter and an inflation catheter disposed within the guide catheter.

FIG. 10 illustrates yet another embodiment of a PFO treatment catheter comprises a high intensity ultrasound transducer.

FIGS. 11-12 illustrate various biocompatible, atraumatic, implantable mechanical devices for the transseptal occlusion or closure of a PFO.

FIGS. 13A-13E illustrate a hook-and-twist mechanical device for occluding or closing a PFO in accordance with this aspect of the invention, where:

FIG. 13A is a cross-sectional view illustrating the deployment of the hook-and-twist device within the PFO tunnel; and

FIGS. 13B-13E are top views illustrating a method of implanting the hook-and-twist device inside the PFO tunnel.

FIG. 14 generally illustrate yet another aspect of the present invention wherein the various PFO treatment catheters and device can be adapted with a location member designed to facilitate detection and location of a PFO, puncture location, as well as maintains the position of the PFO treatment catheter during the treatment process.

DETAILED DESCRIPTION OF THE PRESENT INVENTION

Referring now to the drawings, the flow chart of FIG. 3 describes a method of therapeutically closing or occluding a PFO 1. Generally, the treatment method involves inserting PFO treatment catheter 21 configured to transseptally deliver energy to the secundum 5 and the primum 7 to affect joining or welding of these tissues.

PFO treatment catheter 21, in accordance with the present invention is illustrated in FIG. 4A. PFO treatment catheter 21 should be long enough to extend from an insertion site to interatrial septum 3. Typical lengths for catheter 21 include, but are not limited to, a range of about 50°-200 cm and preferably sized between about 2-15 French. Suitable materials for PFO treatment catheter 21 include, but are not limited to, various polyethylenes, polyurethanes, polysilicones, other biocompatible polymers and materials well known to those skilled in the catheter arts. The interior 22 of catheter 21 is adapted to allow passage of one or more other catheters and components (such as guidewires 31, imaging devices, etc) therethrough. See FIG. 4B. PFO treatment catheter 21 can be further configured to comprise one or more lumens 22 extending its entire length or only a portion thereof. The one or more lumens 22 of catheter 21 can be used as paths for cables, other catheters, guidewire 31, pull wires, insulated wires, fluids, gases, optical fibers, vacuum channels, and any combination thereof.

PFO treatment catheter 21 can be used in conjunction with guidewire 31 so that it can be readily introduced and percutaneously advanced from the insertion site (such as a femoral vein, femoral artery, or other vascular access location) until distal working end 29 is appropriately seated within the patient's heart, at or near, PFO 1. In one possible implementation, guidewire 31 can be inserted into the femoral vein, advanced up the inferior or superior vena cava, into the right atrium and to the interatrial septum 3, near the fossa ovalis 10, and PFO 1.

Penetration of the interatrial septum 3 at a pre-determined location can be accomplished, with or without image guidance. Imagine guidance methods include but are by no means limited to: fluoroscopic; ultrasound (IVUS); intracardiac echo (ICE) ultrasound; magnetic resonance imaging (MRI); and echocardiographic guidance including transesophageal echocardiography (TEE). To penetrate and pass through interatrial septum 3, guidewire 31 can be removed and tissue penetrating device 41 advanced. In one embodiment of the present invention, tissue penetrating device 41 may be a puncturing needle such as conventionally available Brockenbrough needles or other like means. Another possible implementation involves the direct use of guidewire 31 to penetrate interatrial septum 3, eliminating the need to insert and advance separate tissue penetrating device or devices 41. In addition, various other transseptal penetrating methods and devices as disclosed in U.S. provisional applications: Ser. No. 60/477,760, filed Feb. 13, 2003 and entitled “PFO and ASD Closure via Tissue Welding” and Ser. No. 60/474,055, filed May 28, 2003 and entitled “Atrial Transseptal Atrial Access Technology;” the entire contents of which are hereby incorporated by reference and commonly assigned, can also be used to affect penetration of interatrial septum 3 to facilitate the transseptal passage of various devices, including the distal end of PFO treatment catheter 21, into the left atrium of the heart.

As illustrated in FIG. 5A, interatrial septum 3 can be punctured at a number of different locations within region R; however, for the purposes described herein, preferably, penetration of interatrial septum 3 is made at a location where secundum 5 and primum 7 overlap so that both tissue structures are penetrated. When septum 3 is penetrated, an access pathway is created allowing both secundum and primum to be encased between opposed members 51 and enabling access to the left atrium of the heart. As illustrated generally in FIG. 5B, opposed members 51 should be transseptally positioned inside the patient's heart before energy is delivered to the tissues. Opposed members 51 can be used as: (1) a means for coapting the tissues to be joined or welded; (2) a means for supplying compressive force to the tissues; and/or (3) a means for generating sufficient energy in order to heat the coapted tissues to a tissue temperature in a range between about 50°-100° C. One or more heat generating members 53 (for example, RF electrodes 53) can be disposed on opposed members 51 in order to affect tissue heating and application of therapeutic amounts of energy to the encased tissues. As described herein, other configurations are possible.

In the present invention, various energies, energy delivery sources and devices can be employed to increase the native tissue temperatures within a therapeutic range between about 50°-100° C. including: (i) a radiofrequency (RF) generating source coupled to one or more RF electrodes; (ii) a coherent or incoherent source of light coupled to an optical fiber; (iii) a heated fluid coupled to a catheter with a closed channel configured to receive the heated fluid; (iv) a resistive heating source and heating element; (v) a microwave source coupled to a microwave antenna; (vi) an ultrasound power source coupled to an ultrasonic emitter or from external ultrasound; or (vii) any combination of the above. Tissue heating by any of these methods should be tightly controlled to ensure no charring and prevent overheating of the surrounding cardiac tissues. Accordingly, various known temperature sensing means, tissue impedance monitoring techniques, feedback systems, and controls may be incorporated into the present invention and to PFO treatment catheter 21 to allow monitoring of the heating process. Various cooling techniques can be employed (such as the seepage or circulation of various biocompatible liquids, saline, or blood during the heating process as a cooling mechanism). Moreover, such heating systems can be made to focus more energy on the right side of the septum, so that any emboli that are generated will not be allowed to enter the systemic circulation.

For ease of discussion and illustration, and for the remainder of this invention, use of RF energy, in a range of about 100-1000 kHz, supplying power in a range of about 5-50 watts, for duty cycles in a range of about 0.5-20 seconds, will be discussed. The various heat generating members described below are either monopolar or bipolar RF electrodes 53. However, all of the other energy sources and devices described above are equally applicable and may be incorporated into any of the embodiments provided below and used to affect the transseptal joining or welding of tissues to partially or completely, close or occlude, a PFO.

Turning now to FIGS. 6-10 and 11, various embodiments of PFO treatment catheter 21 and catheter assemblies 21, for practicing the joining or welding treatment techniques of the present invention are described.

FIG. 6A illustrates one embodiment of PFO treatment catheter 21 in accordance with the present invention. PFO treatment catheter 21 comprises an elongated shaft having a proximal portion, a distal portion, a proximal inflation member 61, and a distal inflation member 63. Said proximal and distal inflation members 61, 63 are located at a distal working end 29 of catheter 21. Disposed on proximal 61 and distal 63 inflation members may be one or more RF electrodes 53 for tissue heating.

During use, guidewire 31 can be used to advance PFO treatment catheter 21 across and through interatrial septum 3 after interatrial septum 3 has been penetrated. Preferably, PFO treatment catheter 21 is advanced over guidewire 31 until distal inflation member 63 is located on the left atrial side of the interatrial septum 3 while proximal inflation member 61 is located on the right atrial side. To ensure this relative arrangement, these balloon structures 61, 63 can be inflated with contrast fluid, or one or more radio-opaque markers may be disposed on, or adjacent to, the inflation members, so that the desired transseptal positioning of the inflation members can be visually verified, for example, under fluoroscopy. After transseptal positioning of inflation members 61, 63 is visually verified, guidewire 31 may be removed and the tissue coapted together between proximal inflation 61 and distal inflation member 63. A simple method for coapting the tissues may be to expand the inflation members 61, 63 with a fluid (such as contrast solution); a gas (such as carbon dioxide), or any combination thereof. As shown in FIG. 6A, the secundum 5 and primum 7 should be transseptally encased between inflation members 61, 63.

Once coapted, the one or more RF electrodes 53 disposed on the surface of inflation members 61, 63 can be energized to heat the encased tissues and increase native tissue temperatures to about 50°-100° C. In accordance with this aspect of the invention, RF electrodes 53 should be disposed on the surface of the inflations member 61, 63 so that when inflated, these RF electrodes 53 are in direct contact with the tissues to affect efficient tissue heating. RF electrodes 53 can be energized as many times as needed to affect sufficient tissue heating and subsequently heat induced joining of the tissues. As illustrated in FIG. 6B, single monopolar RF electrode 53 can be disposed on the proximal inflation member 61 or alternatively a bipolar RF electrode 53 configuration may be used, wherein in a first electrode 53 is disposed on proximal inflation member 61 and second electrode 53 is disposed on distal inflation member 63. As will be readily appreciated by those skilled in the art, PFO treatment catheter 21 comprising a single monopolar electrode 53 on proximal inflation member 61 can be advantageous in that heating from the right atrial side of the septum 3 can potentially limit or eliminate the potential of any embolic material from being introduced into the systemic atrial circulation. RF electrodes 53 of this embodiment can be energized as many times and for as long as necessary to affect joining of the tissues. To adapt this embodiment of PFO treatment catheter 21 for the welding of the secundum 5 and primum 7, PFO treatment catheter 21 can be configured so that user applied force at the proximal end of PFO treatment catheter 21 is transmitted down elongated shaft 23, which then translates as compressive force supplied to the encased tissues by the proximal 61 and distal 63 inflation members.

RF electrodes 53 can be disposed on the surface of proximal 61 and/or distal 63 inflation members using techniques including: ion implanting, electroplating, sputtering, electro-deposition and chemical and/or adhesive bonding methods; to disposed various RF electrodes 53 on the surface of the proximal 61 and distal 63 inflation members. Electrodes 53 may be formed from gold, platinum, silver, or other materials, preferably, these other materials should be malleable, suitable for in-vivo tissue contact, and thermally conductive.

To verify that a satisfactory level of closure or occlusion has been achieved, contrast TEE, ICE or TCD bubble studies can be performed before catheter is withdrawn from the patient through the passage created during penetration of interatrial septum 3. Preferably, the opening should be small enough so that the body's natural injury response mechanisms will serve to close this left atrial access pathway. PFO treatment catheter 21 can be used in conjunction with a guide or introducer sheath or catheter to facilitate advancement of catheter 21 into and through the tortuous vasculature.

FIGS. 7A and 7B illustrate yet another embodiment of a PFO treatment catheter in accordance with the present invention. In this embodiment, secundum 5 and primum 7 are encased between distal end of PFO treatment catheter 21 and wire assembly 27. Wire assembly 27 can be pre-loaded into the distal working end 29 of catheter 21 and deployed by the user after puncture of the interatrial septum 3 in order to coapt the tissues.

FIG. 8 illustrates another embodiment of the present invention wherein PFO treatment catheter 21 comprised of two coiled RF electrodes 71, 73 disposed at the distal working end 29 of catheter 21. In this embodiment, coiled RF electrodes 71, 73 are pre-loaded inside PFO treatment catheter 21 and advanced out of distal working end 29 of catheter 21 by user applied pressure or force on a release element (not shown) located at the proximal end of catheter 21. As illustrated in FIG. 8, RF coils 71, 73 are transseptally deployable. The tissues are coapted by encasing them between RF coils 71, 73 that may be tension loaded. Alternatively, coiled RF electrodes 71, 73 may be disposed, for example on a wire or other like means, so that the user applied pull-back force on the wire serves to coapt and/or compress the tissues. Preferably, coiled RF electrodes 71, 73 should be made from any biocompatible material, including but not limited to: any nickel-titantium (Nitinol) alloy and other shape metal alloys, stainless steel, platinum, noble metals, and other like materials. Appropriate positioning of the RF coils 71, 73 may be visualized under fluoroscopy, x-ray, ultrasound, TEE, ICE, or using other conventional imaging techniques.

In this aspect of the invention, joining or welding of the tissues may be affected at a single tissue contact point; at multiple tissue contacts points; or alternatively along a seam in order to affect partial or complete closure of the PFO tunnel. To this end, RF coils 71, 73 may be configured with one or more selectively spaced RF electrodes 71, 73 disposed on the coiled surfaces of RF coils 71, 73 in order to create the desired tissue contact point, pattern or seam given a pre-selected size and shape.

FIG. 9 illustrates yet another embodiment of present invention wherein a PFO treatment catheter assembly 21 is provided. As shown in FIG. 9, PFO treatment catheter assembly 21 is comprised of a guide catheter 81 and inflation catheter 91 disposed therein. As shown in FIG. 9, guide catheter 81 is comprised of an elongated shaft 83 having proximal 85 and distal 87 portion, and one or more lumens extending completely and/or partially therethrough with at least one lumen adapted to allow insertion and advancement of inflation catheter 91. Inflation catheter 91 is comprised of elongated inflation catheter shaft 93 having a proximal inflation catheter portion 95, a distal inflation catheter portion 97, one or more lumens extending completely or partially therethrough, and inflation member 99 located at a distal catheter working end 101.

During operation, guide catheter 81 should be disposed on the right atrial side while the distal working end of inflation catheter 101 is transseptally passed through until inflation member 99 is located on the left atrial side. Various tissue penetrating devices 41, as well as guidewires 31, can be used to facilitate the transseptal advancement of the distal working end of inflation catheter 101 into the left atrium (as well as insertion and advancement of guide catheter 81 to the interatrial septum 3). Once appropriately advanced, inflation member 99 can be inflated to coapt and encase the secundum 5 and primum 7 between distal end 89 of guide catheter 81 and inflation member 99. In one embodiment of the invention, one or more RF electrodes 53 can be disposed on distal end 89 of guide catheter 81 and on inflation member 99 located on the inflation catheter so that bipolar RF energy may be used to join or weld the tissues. In another embodiment, one or more monopolar RF electrodes 53 can be disposed on distal end 89 of the guide catheter 81 and energized. Once the energy delivery is completed, inflation member 99 may be deflated, and with inflation catheter 91 and guide catheter 81, withdrawn from the patient.

FIG. 10 illustrates yet another embodiment of the present invention. In this embodiment, high intensity ultrasound catheter 111 as described in U.S. Pat. No. 6,635,054, the entire contents of which are hereby incorporated by reference and modified to suit the aims of the present invention, is employed to affect joining or welding of secundum 5 and primum 7 to close or occlude PFO 1.

As illustrated, the high intensity ultrasound catheter 111 is comprised of catheter shaft 113, first balloon 115, and gas-filled second balloon 117 located at distal working end of catheter 111. Comprised within first balloon 115 is gas filled inner “structural” balloon 121 and liquid filled outer “reflector” balloon 123, which is coaxially disposed around the inner structural balloon such that when both structural 121 and reflector 123 balloons are in a deflated configuration, reflector balloon 123 closely overlies deflated structural balloon 121. As shown in FIG. 10, disposed within the inner structural balloon 121 is ultrasound transducer 125 adapted to emit high intensity ultrasound energy.

In use, a high intensity ultrasound catheter 111 is positioned so that first balloon 115 is disposed within right atrium and second balloon 117 is disposed within the left atrium. Once appropriately positioned, first 115 and second 117 balloons may be inflated and the tissues to be joined or welded, coapted between first 115 and second 117 balloon. Ultrasound transducer 125 located within first balloon 115 is energized and acoustic energy projected forward into the tissues coapted between the two 115, 117 inflated balloons.

Because second balloon 117 is gas filled (and because high intensity acoustic waves cannot and do not travel well in gases) second balloon 117 functions to reflect any excess energy, preventing overheating in the left atrium and minimizing the risk of left side embolic events.

Briefly, the forward projection of acoustic energy from ultrasound transducer 125 into the coapted tissues is achieved by the configuration and shape of gas-filled structural balloon 121 and fluid filled reflector balloon 123 within first balloon 115, as described in more detail in U.S. Pat. No. 6,635,054. As described therein, gas-filled structural balloon 121 is comprised of active wall 127 which is formed from a flexible material and has a specific shape or configuration (parabolic or conical shape) when inflated. The shape of active wall 127, in conjunction with air-filled reflector balloon 123, functions to refract and project the acoustic waves 128 generated by the ultrasound transducer distally forward as illustrated in FIG. 10. Once sufficient energy is applied, first 115 (including structural 121 and reflector 123 balloons) and second 117 balloons are deflated and withdrawn through the access pathway created when interatrial septum 3 is penetrated.

FIGS. 11-12 are diagrammatic representations of yet another aspect of the present invention wherein devices 141 adapted for the efficient occlusion or closure of a PFO are shown. In accordance with the present invention, these devices 141 include various clips, staples, T-bar, Z-part devices that can be transseptally deployed. Preferably, such devices 141 should be formed from biocompatible materials such as various nickel-titanium and other shape memory alloys, stainless steel, platinum and other like materials. Preferably these devices 141 should not require the subsequent device endothelization, but rather should result in immediate, partial or complete, closure or occlusion of a PFO by coapting secundum and primum. Devices 141 can be delivered and deployed, however, a further implementation of this aspect of the invention, is devices 141 being heat secured after delivery. As will be readily appreciated by those skilled in the art, one fairly significant issue related to use of heat generating members (such as RF electrodes) is that heated tissue frequently adheres or sticks to the member. (For further discussion of this issue, please refer to U.S. Pat. No. 4,492,231, the entire contents of which are hereby incorporated by reference.) While this may pose technical difficulties in other circumstances, this embodiment of the invention utilizes this feature to ensure that the coapted tissues and devices 141 are securely heat fixed together and implanted in the patient to avoid or prevent device migration, dislodgement, etc. Accordingly, various devices 141 can be configured to comprise one or more RF electrodes using monopolar or bipolar RF energy to affect heat attachment of devices 141.

FIGS. 13A-13E illustrate yet another aspect of the present invention referred to herein as “hook-and-twist” device 151. Hook-and-twist device 151 shown in FIG. 12 is comprised of an elongated neck 153 disposed between proximal hook 155 and distal hook 157. As illustrated in FIG. 12 and unlike the other devices illustrated in FIG. 11, “hook-and-twist” device 151 of this embodiment is advanced into and through the tunnel-like opening of the PFO 1. The proximal and distal hooks 155, 157 are designed to atraumatically engage and catch PFO 1 from the right and left atrial sides of PFO from within the PFO tunnel or PFO opening. To implant device 151, it is wound until the tissues engaged by device 151 are squeezed together and become taunt; and the increased tautness in the tissues serves to decrease the likelihood of PFO 1 from opening. In this embodiment, after device 151 has been appropriately twisted, device 151 would be disengaged from a delivery catheter and thus implanted. In a related but different embodiment, hook-and-twist device 151 and the tissues encased in by hook-and-twist device 151 can be configured to comprise one or more monopolar electrodes to affect welding of the encased tissues and heat attachment of implanted device 151 inside the patient.

As discussed above, sticking of heated tissues to the various heating elements 53, RF coils 71, 73, etc. should be avoided in those non-implant embodiments of the present invention. To this end, several techniques can be employed. For instance, various non-adhesive biocompatible gels, hydrogels, liquids (such as saline) may be employed to facilitate the release of the heated tissues from various PFO treatment catheters 21 of the present invention. Preferably, such materials are bio-absorbable. Also, these materials should be electrically conductive when used in conjunction with RF energy based components creating a complete electrical circuit. These materials may be disposed on the external surface of catheter 21 or extruded from one or more ports disposed at or near the distal ends of the various devices (coils 71, 73, balloons 61, 63) and catheters 21 of the present invention. In accordance with this aspect of the invention, inflation members 61, 63 may be formed of porous material in order to facilitate seepage of saline or other like liquids to the tissues being heated. This seepage facilitates char-fee heating, ready release of tissues from the heating elements, and/or completion of the electrical circuit to enhance and promote the energy delivery process. In addition, circulation of these materials (as well as blood and/or other biological fluids) can also be provided as a means to promote cooling and heat dissipation during the energy delivery process to prevent issues of overheating, tissue charring, etc.

Detecting and locating PFO 1 is an important aspect of the invention and conventional techniques, including ultrasound, fluoroscopy, TEE, ICE, and ear oximetry techniques can be used for this purpose. In yet another embodiment, of the present invention the various catheters 21 of the present invention can be adaptively shaped to identify and engage certain detectable anatomical structures (such as the annular structure surrounding the fossa ovalis 10) as one means of locating PFO 1 as well as securely positioning PFO treatment catheters 21 and catheter assemblies 21 for penetration of interatrial septum 3 and the energy delivery process. In one embodiment, the various catheters 21 may be configured to further comprise location means 161 complementarily shaped to securely engage the antero-superior portion of the annular tissue structure 162 that typically surrounds the fossa ovalis 10 which is near PFO 1; or location means 161 may alternatively be used to locate the fossa ovalis 10. This aspect of the invention is illustrated in FIG. 14.

In a further aspect of the present invention, the process of joining or welding of the tissues can be immediate leading to PFO 1 closure or occlusion following energy delivery in accordance with the present invention. However, it is also contemplated that joining or welding of the tissues can occur over several days wherein the tissue joining process is mediated in part to the body's healing response to thermal injury. Nevertheless, whether the closure or occlusion of the PFO is immediate or gradual, complete or partial; preferably, the attachment of the primum and secundum to affect PFO 1 closure or occlusion should be permanent.

Finally, while several particular embodiments of the present invention have been illustrated and described, it will be apparent to one of ordinary skill in the art that various modifications can be made to the present invention, including one aspect of one embodiment combined with another aspect of one embodiment. Other obvious adaptations of the present invention include the use of the devices, methods, and systems during minimally invasive surgery.

Also, as will be readily appreciated by those skilled in the art, the present invention described methods and devices that can be used to treat other types of cardiac defect. The general energy-based method for joining tissues is applicable as a therapeutic treatment method for closing other cardiac defects including, but not limited to patent ductus arteriosus, atrial septal defects, and other types of abnormal cardiac openings wherein an effective treatment is to join or weld tissue. Accordingly, the present invention and the claims are not limited merely for the therapeutic treatment of PFO but can be used for closure of occlusion of cardiac defects, body lumens, vessels, etc. Modifications and alterations can be made without departing from the scope and spirit of the present invention and accordingly, it is not intended that the invention be limited, except as by the appended claims. 

1. A treatment method for closing a patent foramen ovale comprising two flap-like tissue structures and which is located on an interatrial septum separating a right and left atrium of a heart; said method comprising the steps of: a) detecting and locating the patent foramen ovale; b) encasing the two flap-like tissue structures between one or more heat generating members; b) energizing the one or more heat generating means; and c) applying a therapeutic amount of energy to join the two overlapping tissue structures at one or more positions of contact.
 2. The method of claim 1, wherein the therapeutic amounts of energy is produced by a proximal heat generating member located in the right atrium of the heart.
 3. The method claim 1, wherein the therapeutic amounts of energy is produced by a distal heat generating member located in the left atrium of the heart.
 4. The method of claim 3, wherein the therapeutic amounts of energy are simultaneously produced by the proximal heat generating member located in the right atrium and the distal heat generating member located within the left atrium.
 5. The method of claim 4, wherein the proximal and distal heat generating members are transseptally deployed.
 6. The method of claim 3 or 4, further comprising the step of: penetrating the interatrial septum of the heart and forming a left atrial access pathway.
 7. The method of claim 1, 2, 3, or 4, wherein the tissues are joined at the one or more points of contact.
 8. The method of claim 1, 2, 3, or 4, wherein the one the tissue are joined along a seam.
 9. The method of claim 1, 2, 3, or 4, wherein the PFO is partially closed.
 10. The method of claim 1, 2, 3, or 4, wherein the PFO is completely closed.
 11. The method of claim 1, 2, 3, or 4, wherein the two overlapping tissue structures are permanently joined.
 12. The method of claim 1, further comprising the step of: applying a lubricating means to prevent sticking of the tissues to the one or more heat generating means.
 13. The method of claim 12, wherein the lubricating means is electrically conductive.
 14. The method of claim 13, further comprising the step of: providing a monitoring means to prevent overheating of cardiac tissues adjacent the encased tissues.
 15. A treatment method for therapeutically closing a patent foramen ovale on an interatrial septum separating a right and left atrium of the heart, said treatment method comprising the steps of: a) determining the location of the patent foramen ovale; and b) applying therapeutic amounts of energy to the septum at or near the location determined in step (a) to induce.
 16. The method of claim 15, wherein the therapeutic amount of energy is applied from the right atrium of the heart.
 17. The method of claim 15, further comprising the step of: a) puncturing the septum on or near the patent foramen ovale and creating an access pathway into the left atrium of the heart.
 18. The method of claim 17, further comprising the steps of: introducing the first heat generating member into the right atrium; and introducing a second heat generating member into the left atrium of the heart.
 19. The method of claim 18, further comprising the step of: energizing the first heat generating member.
 20. The method of claim 18, wherein the first and second heating means are energized simultaneously.
 21. The method of claim 18, wherein the first and second heating means are used in order to apply a compressive force to the septum encased between the first and second heating means.
 22. The method of claim 18, further comprising the step of: introducing a lubricating means to prevent sticking of the septum to the first and second heating means.
 23. The method of claim 22, wherein the lubricating means is also electrically conductive.
 24. A catheter apparatus for closing a patent foramen ovale comprised of two overlapping tissue structures located on an interatrial septum which separates a right and left atrium of the heart, said apparatus comprising: a) a means for locating and detecting the patent foramen ovale; b) a means for puncturing the interatrial septum at, or adjacent, the patent foramen ovale; and c) one or more means for transseptally delivering therapeutic amounts of energy one or more tissue locations in order to affect joining of the overlapping tissue structures.
 25. The apparatus of claim 24, wherein the one or more means for applying compressive force to the interatrial septum.
 26. The apparatus of claim 25, further comprising one or more radio-opaque means. 